WO2017147082A1 - Bifurcated tubular graft for treating tricuspid regurgitation - Google Patents
Bifurcated tubular graft for treating tricuspid regurgitation Download PDFInfo
- Publication number
- WO2017147082A1 WO2017147082A1 PCT/US2017/018741 US2017018741W WO2017147082A1 WO 2017147082 A1 WO2017147082 A1 WO 2017147082A1 US 2017018741 W US2017018741 W US 2017018741W WO 2017147082 A1 WO2017147082 A1 WO 2017147082A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- leg
- stent
- valve
- tubular
- medical device
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
- A61F2/2418—Scaffolds therefor, e.g. support stents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2427—Devices for manipulating or deploying heart valves during implantation
- A61F2/243—Deployment by mechanical expansion
- A61F2/2433—Deployment by mechanical expansion using balloon catheter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/844—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents folded prior to deployment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2002/065—Y-shaped blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/006—Y-shaped
Definitions
- the human heart includes four chambers, which are the left and right atrium and the left and right ventricles.
- the mitral valve which allows blood flow in one direction, is positioned between the left ventricle and left atrium.
- the tricuspid valve is positioned between the right ventricle and the right atrium.
- the aortic valve is positioned between the left ventricle and the aorta, and the pulmonary valve is positioned between the right ventricle and pulmonary artery.
- the heart valves function in concert to move blood throughout the circulatory system. If the valves of the heart do not function properly, due either to disease or congenital defects, the circulation of the blood may be compromised.
- Diseased heart valves may be stenotic, wherein the valve does not open sufficiently to allow adequate forward flow of blood through the valve, and/or incompetent, wherein the valve does not close completely. Incompetent heart valves cause regurgitation or excessive backward flow of blood through the valve when the valve is closed. For example, certain diseases of the heart valves can result in dilation of the heart and one or more heart valves. When a heart valve annulus dilates, the valve leaflet geometry deforms and causes ineffective closure of the valve leaflets. The ineffective closure of the valve can cause regurgitation of the blood, accumulation of blood in the heart, and other problems.
- Valvular regurgitation can occur when the valve leaflets (for the tricuspid and mitral valve) or the valve cusps (for the aortic or pulmonary valve) do not coapt properly when the valve is closed. This can be caused by a variety of disease processes, including, e.g., leaflet or cusp retraction, annular dilatation (e.g., annuloaortic ectasia, mitral or tricuspid annular dilatation, etc.), etc. Also, the leaflets or cusps of a valve can prolapse (or fall back) as a result of stretching or rupture of their support system. What all these processes have in common is that an orifice (a regurgitant orifice) remains after valve closure through which blood can flow backwards (i.e., not in the intended direction), thus creating valve regurgitation.
- an orifice a regurgitant orifice
- valve replacement surgery in which damaged leaflets are excised and the annulus is sculpted to receive a replacement valve.
- annuloplasty Another repair technique that has been shown to be effective in treating incompetence is annuloplasty, in which the effective size of the valve annulus is contracted by attaching a prosthetic annuloplasty repair segment or ring to an interior wall of the heart around the valve annulus.
- the annuloplasty ring reinforces the functional changes that occur during the cardiac cycle to improve coaptation and valve integrity.
- annuloplasty rings help reduce reverse flow or regurgitation while permitting good hemodynamics during forward flow.
- Annuloplasty rings may be stiff or flexible, may be open or closed, and may have a variety of shapes including circular, D-shaped, or C-shaped.
- the configuration of the ring is generally based on the shape of the heart valve being repaired or on the particular application.
- the tricuspid valve is generally circular and the mitral valve is generally D- shaped.
- C-shaped rings may be used for tricuspid valve repairs, for example, because it allows a surgeon to position the break in the ring adjacent the atrioventricular (AV) node, thus avoiding the need for suturing at that location. All of these prior art procedures are complicated repairs that involve risks to the patient.
- the present invention improves blood flow through the tricuspid valve and prevents regurgitation and is delivered and implanted minimally invasively thereby reducing risks and improving patient safety.
- a device and method of use is provided for reducing cardiac valve regurgitation, and more particularly, provides a device designed to regulate flow through the tricuspid valve and reduce the likelihood or prevent regurgitation through the tricuspid valve.
- a tubular graft having a Y-shaped configuration includes a tubular main body and a tubular leg portion extending from the tubular main body and being in fluid communication with the tubular main body.
- the tubular main body has a first end extending into the superior vena cava (SVC) and a first stent adjacent the first end of the tubular main body for attaching the tubular main body to the SVC.
- the tubular main body has a second end extending into the inferior vena cava (IVC) and a second stent adjacent the second end for attaching the tubular main body to the IVC.
- the tubular leg portion extends from the tubular main body and is in fluid communication with the tubular main body.
- the tubular leg portion is configured for extending into and through the right atrium and through the tricuspid valve.
- the tubular leg portion has a third stent adjacent a distal end of the tubular leg portion to hold open the tricuspid valve.
- a bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm).
- the bioprosthetic valve is positioned in the tubular portion and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm).
- the bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm). In yet another embodiment, the bioprosthetic valve is positioned in the tubular leg portion and abuts the third stent.
- a bifurcated endograft has a Y-shaped configuration and includes a first leg, a second leg, and a third leg, all in fluid communication with each other.
- the first leg has a first length and is configured for extending into the SVC and a first stent adjacent a distal end of the first leg for attaching the first leg to the SVC.
- the second leg has a second length and is configured for extending into the IVC and a second stent adjacent the distal end of the second leg for attaching the second leg to the IVC.
- a third leg has a third length and is configured for extending into the right atrium and through the tricuspid valve.
- the third leg has a third stent adjacent a distal end of the third leg to hold open the tricuspid valve.
- a bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm).
- the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm).
- the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm).
- the bioprosthetic valve is positioned in the third leg and abuts the third stent.
- FIG. 1 schematically illustrates a cross-section of the heart showing blood flow throughout the heart
- FIG. 2 schematically illustrates a vertical cross-section of the heart
- FIG. 3 schematically illustrates a horizontal cross-section of the heart in diastole showing valve operation
- FIG. 4 schematically illustrates a horizontal cross-section of the heart in systole showing valve operation
- FIG. 5 is a plan view of the tubular graft
- FIG. 6 is a plan view, in cross-section, showing the tubular graft, the stents for attaching the graft to the vessel walls, and a prosthetic valve;
- FIG. 7 schematically illustrates the tubular graft implanted in the SVC, IVC, and extending across the tricuspid valve;
- FIG. 8 is a schematic view of the tubular graft in cross-section, implanted in the SVC,
- FIG. 9 schematically illustrates the tubular graft in cross-section and implanted in the SVC, IVC, and across the tricuspid valve, with the prosthetic valve abutting the third stent;
- FIG. 10 schematically illustrates in cross-section the tubular endograft implanted in the SVC, IVC, and across the tricuspid valve
- FIG. 11 schematically illustrates in cross-section the tubular endograft implanted in the SVC, IVC, and across the tricuspid valve, with the bioprosthetic valve abutting the third stent.
- FIG. 1 a cross-sectional view of a heart is shown to illustrate blood flow throughout the heart.
- Deoxygenated blood returning from the body comes into heart 100 from either superior vena cava 126 or inferior vena cava 116 and collects in right atrium 122.
- Right atrium 122 contracts to pump the blood through tricuspid valve 118 where it flows into right ventricle 114.
- Right ventricle 114 contracts to send the blood through pulmonary valve 120 into pulmonary artery 124 where it goes into the lungs (not shown).
- the oxygenated blood returning from the lungs flows through pulmonary veins 102 where it flows into left atrium 101.
- Left atrium 101 contracts sending the blood through bicuspid or mitral valve 104 and into left ventricle 108.
- left ventricle 108 contracts, the blood is sent through aortic valve 106 and into aorta 128.
- Left ventricle 108 and right ventricle 114 are separated by ventricular septum 110.
- left ventricle 108 when left ventricle 108 expands to take in blood through mitral valve 104 from left atrium 101, left ventricle 108 may also suck blood back into the left ventricle 108 from the aorta 128 through the aortic valve 106. This back flow of blood from aorta 128 into left ventricle 108 can occur if the aortic valve 106 is not properly functioning.
- a patient's heart is normally arrested and the patient is placed on cardiopulmonary bypass so that a surgery on the aortic valve 106 can be performed.
- FIG. 2 a more detailed vertical cross-section of heart 100 is shown.
- Blood first collects in right atrium 122 from superior vena cava 126 or other veins.
- Right atrium 122 also includes right auricle 142.
- Tricuspid valve 118 is made up of three cusps: posterior cusp 176, septal cusp 178, and anterior cusp 180 (shown retracted).
- Right ventricle 114 has a number of muscles that contract to send blood out of right ventricle 114.
- right ventricle 114 Some of the muscles in right ventricle 114 include right anterior papillary muscle 174 (shown cut), and right posterior papillary muscle 172. Other parts of the anatomy of right ventricle 114 includes conus arteriosis 156, supra ventricular crest 152, and moderator band 160 and septal band 162 of septal marginal trabacula 164.
- the blood outflow to the pulmonary trunk is marked by arrow 154. Pulmonary trunk is shown as 138.
- the blood returning from the lungs returns by left pulmonary veins 134 and right pulmonary veins 136 where it collects in left atrium 101. Left atrium 101 also includes left auricle 138.
- mitral valve 104 When left atrium 101 contracts, blood is sent through mitral valve 104 which is made up of posterior cusp 132 and anterior cusp 130. Blood flows through mitral valve 104 and into left ventricle 108. Muscles in the left ventricle include left posterior papillary muscle 170, left anterior ⁇ papillary muscle 168. Septum 110 separates left ventricle 108 from right ventricle 114. Septum 110 includes the muscular part of intraventricular septum 186, interventricular part of the membranous septum 182, and the atrial ventricular part of membranous septum 184.
- aortic valve 106 When left ventrical 108 contracts, blood is sent through aortic valve 106 which includes left semi-lunar cusp 146, posterior semi-lunar (non-coronary) cusp 148, and right semi-lunar cusp 150. Most of the blood flows through aortic valve 106 and into ascending aorta 128, although some of the blood is diverted into the openings of coronary arteries 140.
- Pulmonary valve 120 is shown in a closed position. Pulmonary valve 120 includes anterior semi-lunar cusp 198, right semi-lunar cusp 190, and left semi-lunar cusp 192. Aortic valve 106 is also shown in a closed position. Aortic valve 106 includes right (coronary) semi-lunar cusp 150, left (coronary) semi-lunar cusp 146, and posterior (non-coronary) semi-lunar cusp 148. The circumflex branch of the left coronary artery is labeled as reference number 208.
- Mitral valve 104 (between left atrium 101 and left ventricle 108) is shown in an open position. Mitral valve 104 includes anterior cusp 130, posterior cusp 132, and commissural cusps 131. There is also left fibrous ring 206 of mitral valve 104.
- Tricuspid valve 118 between the right atrium 122 and the right ventricle 114 is shown in an open position and includes anterior cusp 180, septal cusp 178, and posterior cusp 176.
- Surrounding tricuspid valve 118 is a right fibrous ring of tricuspid valve 198.
- Membranous septum 110 includes intraventricular part 182 (shown by a broken line) and atrial-ventricular part 184.
- Right coronary artery is shown as 196, and left coronary artery is shown as 197.
- Left fibrous trigone is shown as 194, and conus arteriosis is shown as 156.
- FIG. 4 is the heart in systole viewed from the base with the atria removed. All of the parts are essentially the same as in FIG. 3, however, in this figure, aortic valve 106 and pulmonary valve 120 are shown open and tricuspid valve 118 and mitral valve 104 are shown closed. Again, pulmonary valve 120 has anterior semi-lunar cusp 188, right semi-lunar cusp 190, and left semi-lunar cusp 192. Aortic valve 106 is made up of right (coronary) semi-lunar cusp 150, left (coronary) semi-lunar cusp 146, and posterior (non- ⁇ coronary) semi-lunar cusp 148.
- Mitral valve 104 is shown with anterior cusp 130 and posterior cusp 132 surrounded by left fibrous ring 206.
- Tricuspid valve 118 is shown with anterior cusp 180, septal cusp 178, posterior cusp 176, surrounded by right fibrous ring of tricuspid valve 198.
- Right coronary artery is shown as 196 with atrial ventricular branch 202 of right coronary artery 196 and posterior interventricular branch 204 of right coronary artery 196 showing.
- Left coronary artery 197 is also shown.
- Other parts of the heart shown in B are the same as those shown in A.
- the oxygenated blood of the body originates in heart 100 and is pumped by the left ventricle (not shown) into aorta 128. From aorta 128, some blood is supplied to heart 100 through right coronary artery 196 and left coronary artery 197, the remaining blood branches throughout the rest of the body.
- a first branch, subclavian artery feeds axillary artery which turns into brachial artery to feed blood to the arms.
- Brachial artery in turn feeds radial artery and ulnar artery.
- Another branch off of aorta 128 is common carotid artery which feeds blood to the head. Superior mesenteric artery and inferior mesenteric artery feed blood to the abdomen.
- the common iliac artery branches into external iliac artery and femoral artery.
- One of the branches of femoral artery is popliteal artery which branches into anterior tibial artery, posterior tibial artery, and dorsalis pedis artery.
- Peroneal artery branches off of external iliac artery.
- the deoxygenated blood returns to heart 100 through the venous system.
- Some blood returning from the legs flows into posterior tibial vein, and anterior tibial vein, which feed into popliteal vein, and flows into femoral vein.
- Another vein in the legs is great saphenous vein which also feeds into femoral vein.
- Blood then flows into either internal iliac vein or external iliac vein which then flow into common iliac vein to return to heart 100 via inferior vena cava 284.
- Other branches feeding into inferior vena cava 284 include hepatic vein.
- Blood returning from the arms flows into ulnar vein, radial vein, brachial vein, or basilic vein, and flows into axillary vein. Blood flows from axillary vein into left or right innominate vein which flows into superior vena cava. Blood also flows into superior vena cava 278 from right subclavian vein, and from external jugular vein and internal jugular vein.
- a tubular graft 220 having a Y-shaped configuration includes a tubular main body 222 and a tubular leg portion 224 extending from the tubular main body and being in fluid communication with the tubular main body.
- the tubular main body 222 has a first end 226 extending into the superior vena cava (SVC) 228, and a first stent 230 adjacent the first end of the tubular main body for attaching the tubular main body to the SVC.
- SVC superior vena cava
- the tubular main body 222 has a second end 232 extending into the inferior vena cava (IVC) 234 and a second stent 236 adjacent the second end for attaching the tubular main body to the IVC.
- the tubular leg portion 224 extends from the tubular main body 222 and is in fluid communication with the tubular main body.
- the tubular leg portion 224 is configured for extending into and through the right atrium 238 and through the tricuspid valve 240.
- the tubular leg portion has a third stent 242 adjacent a distal end 244 of the tubular leg portion to hold open the tricuspid valve.
- a bioprosthetic valve 246 is positioned in the tubular leg portion 224 and spaced proximal to the third stent 242 a distance 248 in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm).
- the bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm).
- the bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm).
- the bioprosthetic valve 246 is positioned in the tubular leg portion 224 and abuts 250 the third stent 246.
- a bifurcated endograft 260 has a Y-shaped configuration 262 and includes a first leg 264, a second leg 266, and a third leg 268, all in fluid communication with each other.
- the first leg has a first length 270 and is configured for extending into the SVC 272, and a first stent 274 adjacent a distal end 276 of the first leg for attaching the first leg to the SVC.
- the second leg 266 has a second length 278 and is configured for extending into the IVC 280, and a second stent 282 adjacent the distal end 284 of the second leg for attaching the second leg to the IVC.
- the third leg has a third length 286 and is configured for extending into the right atrium 288 and through the tricuspid valve 290.
- the third leg has a third stent 292 adjacent a distal end 294 of the third leg to hold open the tricuspid valve.
- a bioprosthetic valve 296 is positioned in the third leg 268 and spaced proximal to the third stent 292 a distance 298 in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm).
- the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm).
- the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm).
- the bioprosthetic valve 296 is positioned in the third leg 268 and is proximal to the stent and abuts 300 the stent.
- the tubular graft 220 or tubular endograft 260 are formed from a flexible material such as PTFE, ePTFE, polyester, urethane, DACRON ® , TEFLON ® , or other distensible polymer material.
- the diameter of the tubular graft and tubular endograft as well as the length of the legs will vary depending on the size of the patient's heart, SVC, IVC and tricuspid valve.
- the bioprosthetic valve 246, 296 disclosed herein is well known in the art.
- a 23 mm Edwards Sapien valve manufactured by Edwards Lifesciences, Irvine, CA
- the valve can be collapsed during delivery and expanded in a known manner.
- the first, second and third stents described herein are balloon expandable stents of the kind well known in the art.
- the stents plastically deform when expanded using a balloon in conjunction with a delivery catheter.
- a balloon expandable stent is the VISION ® stent manufactured by Abbott Cardiovascular Systems, Inc., Santa Clara, CA.
- the VISION ® stent is balloon expandable and made from a cobalt-chromium alloy to enhance visibility under fluoroscopy during stent delivery.
- the stents herein are attached to the tubular graft by known means, such as an adhesive. Upon expansion, the first, second and third stents form a seal with the SVC, IVC, and tricuspid valve, respectively.
- the tubular graft 220 or bifurcated endograft 260 have a bifurcated or Y-shaped configuration as disclosed herein.
- the tubular graft and tubular endograft can be mounted on a bifurcated balloon delivery catheter system similar to that shown in U.S. Patent No.
- the catheter shown in the '558 patent (FIGS. 28 A - 29) is designed to deliver a bifurcated stent in the coronary arteries, but it can be modified to carry and deliver the Y-shaped tubular graft 220 and tubular endograft 260 to the SVC, IVC and tricuspid valve.
- the present invention graft can be delivered percutaneously and implanted in the SVC, IVC and tricuspid valve using a modified version of bifurcated delivery catheter disclosed in the '558 patent.
Abstract
A lubricated tubular graft (220) is implanted in the inferior vena cava and the superior vena cava in order to control the inflow of blood to the right atrium. A bifurcated leg (224) with a non-collapsing stent (242) extends across the tricuspid valve. A bioprosthetic valve (246) is positioned proximal of the stent in the bifurcated leg in order to regulate flow through the tricuspid valve and to eliminate tricuspid regurgitation.
Description
BIFURCATED TUBULAR GRAFT FOR TREATING TRICUSPID REGURGITATION
BACKGROUND
The human heart includes four chambers, which are the left and right atrium and the left and right ventricles. The mitral valve, which allows blood flow in one direction, is positioned between the left ventricle and left atrium. The tricuspid valve is positioned between the right ventricle and the right atrium. The aortic valve is positioned between the left ventricle and the aorta, and the pulmonary valve is positioned between the right ventricle and pulmonary artery. The heart valves function in concert to move blood throughout the circulatory system. If the valves of the heart do not function properly, due either to disease or congenital defects, the circulation of the blood may be compromised. Diseased heart valves may be stenotic, wherein the valve does not open sufficiently to allow adequate forward flow of blood through the valve, and/or incompetent, wherein the valve does not close completely. Incompetent heart valves cause regurgitation or excessive backward flow of blood through the valve when the valve is closed. For example, certain diseases of the heart valves can result in dilation of the heart and one or more heart valves. When a heart valve annulus dilates, the valve leaflet geometry deforms and causes ineffective closure of the valve leaflets. The ineffective closure of the valve can cause regurgitation of the blood, accumulation of blood in the heart, and other problems. Valvular regurgitation can occur when the valve leaflets (for the tricuspid and mitral valve) or the valve cusps (for the aortic or pulmonary valve) do not coapt properly when the valve is closed. This can be caused by a variety of disease processes, including, e.g., leaflet or cusp retraction, annular dilatation (e.g., annuloaortic ectasia, mitral or tricuspid annular dilatation, etc.), etc. Also, the leaflets or cusps of a valve can prolapse (or fall back) as a result of stretching or rupture of their support system. What all these processes have in common is that an orifice (a regurgitant orifice) remains after valve closure through which blood can flow backwards (i.e., not in the intended direction), thus creating valve regurgitation.
Diseased or damaged heart valves can be treated by valve replacement surgery, in which damaged leaflets are excised and the annulus is sculpted to receive a replacement valve. Another repair technique that has been shown to be effective in treating incompetence is annuloplasty, in which the effective size of the valve annulus is contracted by attaching a prosthetic annuloplasty repair segment or ring to an interior wall of the heart around the valve
annulus. The annuloplasty ring reinforces the functional changes that occur during the cardiac cycle to improve coaptation and valve integrity. Thus, annuloplasty rings help reduce reverse flow or regurgitation while permitting good hemodynamics during forward flow.
Annuloplasty rings may be stiff or flexible, may be open or closed, and may have a variety of shapes including circular, D-shaped, or C-shaped. The configuration of the ring is generally based on the shape of the heart valve being repaired or on the particular application. For example, the tricuspid valve is generally circular and the mitral valve is generally D- shaped. Further, C-shaped rings may be used for tricuspid valve repairs, for example, because it allows a surgeon to position the break in the ring adjacent the atrioventricular (AV) node, thus avoiding the need for suturing at that location. All of these prior art procedures are complicated repairs that involve risks to the patient. The present invention improves blood flow through the tricuspid valve and prevents regurgitation and is delivered and implanted minimally invasively thereby reducing risks and improving patient safety.
SUMMARY OF THE INVENTION
A device and method of use is provided for reducing cardiac valve regurgitation, and more particularly, provides a device designed to regulate flow through the tricuspid valve and reduce the likelihood or prevent regurgitation through the tricuspid valve.
In one embodiment, a tubular graft having a Y-shaped configuration includes a tubular main body and a tubular leg portion extending from the tubular main body and being in fluid communication with the tubular main body. The tubular main body has a first end extending into the superior vena cava (SVC) and a first stent adjacent the first end of the tubular main body for attaching the tubular main body to the SVC. The tubular main body has a second end extending into the inferior vena cava (IVC) and a second stent adjacent the second end for attaching the tubular main body to the IVC. The tubular leg portion extends from the tubular main body and is in fluid communication with the tubular main body. The tubular leg portion is configured for extending into and through the right atrium and through the tricuspid valve. The tubular leg portion has a third stent adjacent a distal end of the tubular leg portion to hold open the tricuspid valve. A bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm). In one embodiment, the bioprosthetic valve is positioned in the tubular portion and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm). In another embodiment, the bioprosthetic
valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm). In yet another embodiment, the bioprosthetic valve is positioned in the tubular leg portion and abuts the third stent.
In another embodiment, a bifurcated endograft has a Y-shaped configuration and includes a first leg, a second leg, and a third leg, all in fluid communication with each other. The first leg has a first length and is configured for extending into the SVC and a first stent adjacent a distal end of the first leg for attaching the first leg to the SVC. The second leg has a second length and is configured for extending into the IVC and a second stent adjacent the distal end of the second leg for attaching the second leg to the IVC. A third leg has a third length and is configured for extending into the right atrium and through the tricuspid valve. The third leg has a third stent adjacent a distal end of the third leg to hold open the tricuspid valve. A bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm). In another embodiment, the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm). In another embodiment, the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm). In yet another embodiment, the bioprosthetic valve is positioned in the third leg and abuts the third stent. BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 schematically illustrates a cross-section of the heart showing blood flow throughout the heart;
FIG. 2 schematically illustrates a vertical cross-section of the heart;
FIG. 3 schematically illustrates a horizontal cross-section of the heart in diastole showing valve operation;
FIG. 4 schematically illustrates a horizontal cross-section of the heart in systole showing valve operation;
FIG. 5 is a plan view of the tubular graft;
FIG. 6 is a plan view, in cross-section, showing the tubular graft, the stents for attaching the graft to the vessel walls, and a prosthetic valve;
FIG. 7 schematically illustrates the tubular graft implanted in the SVC, IVC, and extending across the tricuspid valve; FIG. 8 is a schematic view of the tubular graft in cross-section, implanted in the SVC,
IVC, and across the tricuspid valve;
FIG. 9 schematically illustrates the tubular graft in cross-section and implanted in the SVC, IVC, and across the tricuspid valve, with the prosthetic valve abutting the third stent;
FIG. 10 schematically illustrates in cross-section the tubular endograft implanted in the SVC, IVC, and across the tricuspid valve; and
FIG. 11 schematically illustrates in cross-section the tubular endograft implanted in the SVC, IVC, and across the tricuspid valve, with the bioprosthetic valve abutting the third stent.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
Referring to FIG. 1, a cross-sectional view of a heart is shown to illustrate blood flow throughout the heart. Deoxygenated blood returning from the body comes into heart 100 from either superior vena cava 126 or inferior vena cava 116 and collects in right atrium 122. Right atrium 122 contracts to pump the blood through tricuspid valve 118 where it flows into right ventricle 114. Right ventricle 114 contracts to send the blood through pulmonary valve 120 into pulmonary artery 124 where it goes into the lungs (not shown). The oxygenated blood returning from the lungs flows through pulmonary veins 102 where it flows into left atrium 101. Left atrium 101 contracts sending the blood through bicuspid or mitral valve 104 and into left ventricle 108. When left ventricle 108 contracts, the blood is sent through aortic valve 106 and into aorta 128. Left ventricle 108 and right ventricle 114 are separated by ventricular septum 110.
If there is a problem with aortic valve 106, when left ventricle 108 expands to take in blood through mitral valve 104 from left atrium 101, left ventricle 108 may also suck blood back into the left ventricle 108 from the aorta 128 through the aortic valve 106. This back flow of blood from aorta 128 into left ventricle 108 can occur if the aortic valve 106 is not
properly functioning. In order to repair a nonfunctioning aortic valve 106, a patient's heart is normally arrested and the patient is placed on cardiopulmonary bypass so that a surgery on the aortic valve 106 can be performed. It is difficult to perform a percutaneous aortic valve 106 repair or replacement while the heart is beating, since blood needs to flow through the heart 100 by flowing into pulmonary veins 102 into left atrium 101, through mitral valve 104 into left ventricle 108 across aortic valve 106 and into aorta 128 to be fed to the rest of the body. If there are a number of tools (not shown) that are blocking the aorta 128 that are being used to operate on aortic valve 106, then this blood flow cannot occur normally. In order to perform a surgery on aortic valve 106 without cardiopulmonary bypass, normal blood flow needs to occur through heart 100 and the rest of the body.
Similar problems of heart surgeries or procedures are encountered when working on mitral valve 104, tricuspid valve 118, pulmonary valve 120, and ventricular septum 110. In order to conduct a successful procedure on an area of heart 100, it is necessary to place an inlet of a pump upstream of the area and an outlet of a pump downstream of the area that is going to be worked on, when the area that will be worked on will be blocked by the tools that are used to perform the procedure.
Referring to FIG. 2, a more detailed vertical cross-section of heart 100 is shown. Blood first collects in right atrium 122 from superior vena cava 126 or other veins. Right atrium 122 also includes right auricle 142. When right atrium 122 contracts, blood is sent through tricuspid valve 118 and into right ventricle 114. Tricuspid valve 118 is made up of three cusps: posterior cusp 176, septal cusp 178, and anterior cusp 180 (shown retracted). Right ventricle 114 has a number of muscles that contract to send blood out of right ventricle 114. Some of the muscles in right ventricle 114 include right anterior papillary muscle 174 (shown cut), and right posterior papillary muscle 172. Other parts of the anatomy of right ventricle 114 includes conus arteriosis 156, supra ventricular crest 152, and moderator band 160 and septal band 162 of septal marginal trabacula 164. The blood outflow to the pulmonary trunk is marked by arrow 154. Pulmonary trunk is shown as 138. The blood returning from the lungs returns by left pulmonary veins 134 and right pulmonary veins 136 where it collects in left atrium 101. Left atrium 101 also includes left auricle 138. When left atrium 101 contracts, blood is sent through mitral valve 104 which is made up of posterior cusp 132 and anterior cusp 130. Blood flows through mitral valve 104 and into left ventricle 108. Muscles in the left ventricle include left posterior papillary muscle 170, left anterior
ο papillary muscle 168. Septum 110 separates left ventricle 108 from right ventricle 114. Septum 110 includes the muscular part of intraventricular septum 186, interventricular part of the membranous septum 182, and the atrial ventricular part of membranous septum 184. When left ventrical 108 contracts, blood is sent through aortic valve 106 which includes left semi-lunar cusp 146, posterior semi-lunar (non-coronary) cusp 148, and right semi-lunar cusp 150. Most of the blood flows through aortic valve 106 and into ascending aorta 128, although some of the blood is diverted into the openings of coronary arteries 140.
Referring now to FIG. 3, is a horizontal cross-section of the heart showing the heart in diastole viewed from the base with the atria removed. Pulmonary valve 120 is shown in a closed position. Pulmonary valve 120 includes anterior semi-lunar cusp 198, right semi-lunar cusp 190, and left semi-lunar cusp 192. Aortic valve 106 is also shown in a closed position. Aortic valve 106 includes right (coronary) semi-lunar cusp 150, left (coronary) semi-lunar cusp 146, and posterior (non-coronary) semi-lunar cusp 148. The circumflex branch of the left coronary artery is labeled as reference number 208. Mitral valve 104 (between left atrium 101 and left ventricle 108) is shown in an open position. Mitral valve 104 includes anterior cusp 130, posterior cusp 132, and commissural cusps 131. There is also left fibrous ring 206 of mitral valve 104.
At the base of FIG. 3 (as viewed) is the posterior intraventricular branch of right coronary artery 204 and the atrial ventricular nodal branch of right coronary artery 202. In the middle of the heart is right fibrous trigone 200. Tricuspid valve 118 between the right atrium 122 and the right ventricle 114 is shown in an open position and includes anterior cusp 180, septal cusp 178, and posterior cusp 176. Surrounding tricuspid valve 118 is a right fibrous ring of tricuspid valve 198. Membranous septum 110 includes intraventricular part 182 (shown by a broken line) and atrial-ventricular part 184. Right coronary artery is shown as 196, and left coronary artery is shown as 197. Left fibrous trigone is shown as 194, and conus arteriosis is shown as 156.
Referring to FIG. 4 is the heart in systole viewed from the base with the atria removed. All of the parts are essentially the same as in FIG. 3, however, in this figure, aortic valve 106 and pulmonary valve 120 are shown open and tricuspid valve 118 and mitral valve 104 are shown closed. Again, pulmonary valve 120 has anterior semi-lunar cusp 188, right semi-lunar cusp 190, and left semi-lunar cusp 192. Aortic valve 106 is made up of right (coronary) semi-lunar cusp 150, left (coronary) semi-lunar cusp 146, and posterior (non-
η coronary) semi-lunar cusp 148. Mitral valve 104 is shown with anterior cusp 130 and posterior cusp 132 surrounded by left fibrous ring 206. Tricuspid valve 118 is shown with anterior cusp 180, septal cusp 178, posterior cusp 176, surrounded by right fibrous ring of tricuspid valve 198. Right coronary artery is shown as 196 with atrial ventricular branch 202 of right coronary artery 196 and posterior interventricular branch 204 of right coronary artery 196 showing. Left coronary artery 197 is also shown. Other parts of the heart shown in B are the same as those shown in A.
The oxygenated blood of the body originates in heart 100 and is pumped by the left ventricle (not shown) into aorta 128. From aorta 128, some blood is supplied to heart 100 through right coronary artery 196 and left coronary artery 197, the remaining blood branches throughout the rest of the body. A first branch, subclavian artery feeds axillary artery which turns into brachial artery to feed blood to the arms. Brachial artery in turn feeds radial artery and ulnar artery. Another branch off of aorta 128 is common carotid artery which feeds blood to the head. Superior mesenteric artery and inferior mesenteric artery feed blood to the abdomen. There is a common iliac artery for both legs. The common iliac artery in turn branches into external iliac artery and femoral artery. One of the branches of femoral artery is popliteal artery which branches into anterior tibial artery, posterior tibial artery, and dorsalis pedis artery. Peroneal artery branches off of external iliac artery.
The deoxygenated blood returns to heart 100 through the venous system. Some blood returning from the legs flows into posterior tibial vein, and anterior tibial vein, which feed into popliteal vein, and flows into femoral vein. Another vein in the legs is great saphenous vein which also feeds into femoral vein. Blood then flows into either internal iliac vein or external iliac vein which then flow into common iliac vein to return to heart 100 via inferior vena cava 284. Other branches feeding into inferior vena cava 284 include hepatic vein. Blood returning from the arms flows into ulnar vein, radial vein, brachial vein, or basilic vein, and flows into axillary vein. Blood flows from axillary vein into left or right innominate vein which flows into superior vena cava. Blood also flows into superior vena cava 278 from right subclavian vein, and from external jugular vein and internal jugular vein.
A device and method of use is provided for reducing cardiac valve regurgitation, and more particularly, the device is designed to regulate flow through the tricuspid valve and reduce the likelihood or prevent regurgitation through the tricuspid valve.
In one embodiment shown in FIGS. 5 - 9, a tubular graft 220 having a Y-shaped configuration includes a tubular main body 222 and a tubular leg portion 224 extending from the tubular main body and being in fluid communication with the tubular main body. The tubular main body 222 has a first end 226 extending into the superior vena cava (SVC) 228, and a first stent 230 adjacent the first end of the tubular main body for attaching the tubular main body to the SVC. The tubular main body 222 has a second end 232 extending into the inferior vena cava (IVC) 234 and a second stent 236 adjacent the second end for attaching the tubular main body to the IVC. The tubular leg portion 224 extends from the tubular main body 222 and is in fluid communication with the tubular main body. The tubular leg portion 224 is configured for extending into and through the right atrium 238 and through the tricuspid valve 240. The tubular leg portion has a third stent 242 adjacent a distal end 244 of the tubular leg portion to hold open the tricuspid valve. A bioprosthetic valve 246 is positioned in the tubular leg portion 224 and spaced proximal to the third stent 242 a distance 248 in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm). In one embodiment, the bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm). In another embodiment, the bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm). In yet another embodiment as shown in FIG. 9, the bioprosthetic valve 246 is positioned in the tubular leg portion 224 and abuts 250 the third stent 246.
In another embodiment, a bifurcated endograft 260 has a Y-shaped configuration 262 and includes a first leg 264, a second leg 266, and a third leg 268, all in fluid communication with each other. The first leg has a first length 270 and is configured for extending into the SVC 272, and a first stent 274 adjacent a distal end 276 of the first leg for attaching the first leg to the SVC. The second leg 266 has a second length 278 and is configured for extending into the IVC 280, and a second stent 282 adjacent the distal end 284 of the second leg for attaching the second leg to the IVC. The third leg has a third length 286 and is configured for extending into the right atrium 288 and through the tricuspid valve 290. The third leg has a third stent 292 adjacent a distal end 294 of the third leg to hold open the tricuspid valve. A bioprosthetic valve 296 is positioned in the third leg 268 and spaced proximal to the third stent 292 a distance 298 in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm). In another embodiment, the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to
20.0 mm). In another embodiment, the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm). In yet another embodiment as shown in FIG. 11, the bioprosthetic valve 296 is positioned in the third leg 268 and is proximal to the stent and abuts 300 the stent.
The tubular graft 220 or tubular endograft 260 are formed from a flexible material such as PTFE, ePTFE, polyester, urethane, DACRON®, TEFLON®, or other distensible polymer material. The diameter of the tubular graft and tubular endograft as well as the length of the legs will vary depending on the size of the patient's heart, SVC, IVC and tricuspid valve.
The bioprosthetic valve 246, 296 disclosed herein is well known in the art. For example, a 23 mm Edwards Sapien valve (manufactured by Edwards Lifesciences, Irvine, CA) can be attached in the third leg 268 or tubular leg portion by using sutures or an adhesive. The valve can be collapsed during delivery and expanded in a known manner.
The first, second and third stents described herein are balloon expandable stents of the kind well known in the art. The stents plastically deform when expanded using a balloon in conjunction with a delivery catheter. One example of a balloon expandable stent is the VISION® stent manufactured by Abbott Cardiovascular Systems, Inc., Santa Clara, CA. The VISION® stent is balloon expandable and made from a cobalt-chromium alloy to enhance visibility under fluoroscopy during stent delivery. The stents herein are attached to the tubular graft by known means, such as an adhesive. Upon expansion, the first, second and third stents form a seal with the SVC, IVC, and tricuspid valve, respectively.
The tubular graft 220 or bifurcated endograft 260 have a bifurcated or Y-shaped configuration as disclosed herein. The tubular graft and tubular endograft can be mounted on a bifurcated balloon delivery catheter system similar to that shown in U.S. Patent No.
8,029,558, assigned to Abbott Cardiovascular Systems, Inc. The catheter shown in the '558 patent (FIGS. 28 A - 29) is designed to deliver a bifurcated stent in the coronary arteries, but it can be modified to carry and deliver the Y-shaped tubular graft 220 and tubular endograft 260 to the SVC, IVC and tricuspid valve. Thus, the present invention graft can be delivered percutaneously and implanted in the SVC, IVC and tricuspid valve using a modified version of bifurcated delivery catheter disclosed in the '558 patent.
In the preceding detailed description, reference to specific embodiments were described. It will, however, be evident that various modifications and changes may be made thereto without departing from the broader spirit and scope of the appended claims. The specification and drawings are, accordingly, to be regarded in an illustrative rather than a restrictive sense.
Claims
1. A medical device for treating tricuspid valve regurgitation, comprising:
a bifurcated endograft having a Y-shaped configuration including a first leg, a second leg and a third leg all in fluid communication;
the first leg having a first length and being configured for extending into the superior vena cava (SVC) and a first stent adjacent a distal end of the first leg for attaching the first leg to the SVC;
the second leg having a second length and being configured for extending into the inferior vena cava (IVC) and a second stent adjacent a distal end of the second leg for attaching the second leg to the IVC;
the third leg having a third length and being configured for extending into the right atrium and through the tricuspid valve;
the third leg having a third stent adjacent a distal end of the third leg to hold open the tricuspid valve; and
a bioprosthetic valve positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm).
2. The medical device of claim 1, wherein the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm).
3. The medical device of claim 1, wherein the bioprosthetic valve is positioned in the third leg and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm).
4. The medical device of claim 1, wherein the third stent has a non-collapsing lattice structure in order to hold open the tricuspid valve.
5. The medical device of claim 1, wherein the bifurcated endograft is formed from PTFE, ePTFE, polyester, urethane, DACRON®, TEFLON®, or other distensible polymeric material.
6. The medical device of claim 1, wherein the first stent, second stent and third stent are balloon expandable and plastically deform when expanded.
7. A medical device for treating tricuspid valve regurgitation, comprising:
a tubular graft having a Y-shaped configuration including a tubular main body
and a tubular leg portion extending from the tubular main body and being in fluid communication;
the tubular main body having first end extending into the superior vena cava (SVC) and a first stent adjacent a first end for attaching the tubular main body to the SVC;
the tubular main body having a second end extending into the inferior vena cava (IVC) and a second stent adjacent a second end for attaching the tubular main body to the IVC;
the tubular leg portion being configured for extending into the right atrium and through the tricuspid valve;
the tubular leg portion having a third stent adjacent a distal end of the tubular leg portion to hold open the tricuspid valve; and
a bioprosthetic valve positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 1.1811 in. (1.0 mm to 30.0 mm).
8. The medical device of claim 7, wherein the bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from
0.1969 in. to 0.7874 in. (5.0 mm to 20.0 mm).
9. The medical device of claim 7, wherein the bioprosthetic valve is positioned in the tubular leg portion and spaced proximal to the third stent a distance in the range from 0.0394 in. to 0.3937 in. (1.0 mm to 10.0 mm).
10. The medical device of claim 7, wherein the third stent has a non-collapsing lattice structure in order to hold open the tricuspid valve.
11. The medical device of claim 7, wherein the bifurcated endograft is formed from PTFE, ePTFE, polyester, urethane, DACRON®, TEFLON®, or other distensible polymeric material.
12. The medical device of claim 7, wherein the first stent, second stent and third stent are balloon expandable and plastically deform when expanded.
13. A medical device for treating tricuspid valve regurgitation, comprising:
a bifurcated endograft having a Y-shaped configuration including a first leg, a second leg and a third leg all in fluid communication;
the first leg having a first length and being configured for extending into the superior vena cava (SVC) and a first stent adjacent a distal end of the first leg for attaching the first leg to the SVC;
the second leg having a second length and being configured for extending into the inferior vena cava (IVC) and a second stent adjacent a distal end of the second leg for attaching the second leg to the IVC;
the third leg having a third length and being configured for extending into the right atrium and through the tricuspid valve;
the third leg having a third stent adjacent a distal end of the third leg to hold open the tricuspid valve; and
a bioprosthetic valve positioned in the third leg proximal to the third stent wherein the bioprosthetic valve abuts the third stent.
14. The medical device of claim 13, wherein the third stent has a non-collapsing lattice structure in order to hold open the tricuspid valve.
15. The medical device of claim 13, wherein the bifurcated endo graft is formed from PTFE, ePTFE, polyester, urethane, DACRON®, TEFLON®, or other distensible polymeric material.
16. The medical device of claim 13, wherein the first stent, second stent and third stent are balloon expandable and plastically deform when expanded.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15/051,045 US10130465B2 (en) | 2016-02-23 | 2016-02-23 | Bifurcated tubular graft for treating tricuspid regurgitation |
US15/051,045 | 2016-02-23 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2017147082A1 true WO2017147082A1 (en) | 2017-08-31 |
Family
ID=58228583
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2017/018741 WO2017147082A1 (en) | 2016-02-23 | 2017-02-21 | Bifurcated tubular graft for treating tricuspid regurgitation |
Country Status (2)
Country | Link |
---|---|
US (3) | US10130465B2 (en) |
WO (1) | WO2017147082A1 (en) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US10722631B2 (en) | 2018-02-01 | 2020-07-28 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of use and manufacture |
WO2021058512A1 (en) | 2019-09-26 | 2021-04-01 | Biotronik Ag | Artificial cardiac valve |
US11185677B2 (en) | 2017-06-07 | 2021-11-30 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
US11511103B2 (en) | 2017-11-13 | 2022-11-29 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
US11654275B2 (en) | 2019-07-22 | 2023-05-23 | Shifamed Holdings, Llc | Intravascular blood pumps with struts and methods of use and manufacture |
US11724089B2 (en) | 2019-09-25 | 2023-08-15 | Shifamed Holdings, Llc | Intravascular blood pump systems and methods of use and control thereof |
US11964145B2 (en) | 2019-07-12 | 2024-04-23 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of manufacture and use |
Families Citing this family (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2017137868A1 (en) | 2016-02-08 | 2017-08-17 | Innoventric Ltd. | Treatment of tricuspid insufficiency |
US10130465B2 (en) * | 2016-02-23 | 2018-11-20 | Abbott Cardiovascular Systems Inc. | Bifurcated tubular graft for treating tricuspid regurgitation |
US20190142571A1 (en) * | 2017-11-13 | 2019-05-16 | Derrick Chu | Branching covered stent-grafts and related deployment systems and methods |
AU2019281515A1 (en) * | 2018-06-08 | 2021-01-14 | Innoventric Ltd. | Systems, methods and devices for treating tricuspid insufficiency |
AU2022221314A1 (en) * | 2021-02-15 | 2023-07-20 | Innoventric Ltd. | Systems, methods, and devices for treating a diseased or otherwise damaged tricuspid valve |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060276813A1 (en) * | 2005-05-20 | 2006-12-07 | The Cleveland Clinic Foundation | Apparatus and methods for repairing the function of a diseased valve and method for making same |
US8029558B2 (en) | 2006-07-07 | 2011-10-04 | Abbott Cardiovascular Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
EP2600798B1 (en) * | 2010-08-03 | 2015-10-28 | Cook Medical Technologies LLC | Two valve caval stent for functional replacement of incompetent tricuspid valve |
Family Cites Families (330)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2701559A (en) | 1951-08-02 | 1955-02-08 | William A Cooper | Apparatus for exfoliating and collecting diagnostic material from inner walls of hollow viscera |
US2845959A (en) | 1956-03-26 | 1958-08-05 | John B Sidebotham | Bifurcated textile tubes and method of weaving the same |
US2990605A (en) | 1957-01-30 | 1961-07-04 | Demsyk Paul | Method of forming artificial vascular members |
US2978787A (en) | 1957-04-18 | 1961-04-11 | Meadox Medicals Inc | Synthetic vascular implants and the manufacture thereof |
US3105492A (en) | 1958-10-01 | 1963-10-01 | Us Catheter & Instr Corp | Synthetic blood vessel grafts |
US3096560A (en) | 1958-11-21 | 1963-07-09 | William J Liebig | Process for synthetic vascular implants |
US3142067A (en) | 1958-11-21 | 1964-07-28 | William J Liebig | Synthetic vascular implants |
US3029819A (en) | 1959-07-30 | 1962-04-17 | J L Mcatee | Artery graft and method of producing artery grafts |
US3657744A (en) | 1970-05-08 | 1972-04-25 | Univ Minnesota | Method for fixing prosthetic implants in a living body |
US3945052A (en) | 1972-05-01 | 1976-03-23 | Meadox Medicals, Inc. | Synthetic vascular graft and method for manufacturing the same |
US3868956A (en) | 1972-06-05 | 1975-03-04 | Ralph J Alfidi | Vessel implantable appliance and method of implanting it |
CH557672A (en) | 1973-07-04 | 1975-01-15 | Vnii Khirurgicheskoi Apparatur | SURGICAL DEVICE WITH MEANS FOR REPLACING VOLLUS ORGANS. |
SE397769B (en) | 1974-11-04 | 1977-11-21 | Gambro Ab | INITIATIVE ELEMENTS FOR USE IN VEHICLE SURGERY AND METHODS OF PRODUCING SUCCESSFUL |
US4061134A (en) | 1975-10-28 | 1977-12-06 | Samuels Peter B | Arterial graft device |
US4047252A (en) | 1976-01-29 | 1977-09-13 | Meadox Medicals, Inc. | Double-velour synthetic vascular graft |
US4041931A (en) | 1976-05-17 | 1977-08-16 | Elliott Donald P | Radiopaque anastomosis marker |
US4140126A (en) | 1977-02-18 | 1979-02-20 | Choudhury M Hasan | Method for performing aneurysm repair |
US4193137A (en) | 1977-05-06 | 1980-03-18 | Meadox Medicals, Inc. | Warp-knitted double-velour prosthesis |
US4159719A (en) | 1977-05-09 | 1979-07-03 | Xomed, Inc. | Moisture-expandable ear wick |
US4130904A (en) | 1977-06-06 | 1978-12-26 | Thermo Electron Corporation | Prosthetic blood conduit |
US4323071A (en) | 1978-04-24 | 1982-04-06 | Advanced Catheter Systems, Inc. | Vascular guiding catheter assembly and vascular dilating catheter assembly and a combination thereof and methods of making the same |
US4202349A (en) | 1978-04-24 | 1980-05-13 | Jones James W | Radiopaque vessel markers |
US4214587A (en) | 1979-02-12 | 1980-07-29 | Sakura Chester Y Jr | Anastomosis device and method |
US4387952A (en) | 1981-03-27 | 1983-06-14 | Spectra-Physics, Inc. | Single axis beam scanner |
CA1204643A (en) | 1981-09-16 | 1986-05-20 | Hans I. Wallsten | Device for application in blood vessels or other difficulty accessible locations and its use |
US4516972A (en) | 1982-01-28 | 1985-05-14 | Advanced Cardiovascular Systems, Inc. | Guiding catheter and method of manufacture |
SE445884B (en) | 1982-04-30 | 1986-07-28 | Medinvent Sa | DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION |
NL8220264A (en) | 1982-07-02 | 1984-05-01 | Gravure Res Inst | METHOD AND APPARATUS FOR ENGRAVING PRINTING. |
US4517687A (en) | 1982-09-15 | 1985-05-21 | Meadox Medicals, Inc. | Synthetic woven double-velour graft |
US4531933A (en) | 1982-12-07 | 1985-07-30 | C. R. Bard, Inc. | Helical ureteral stent |
US4512338A (en) | 1983-01-25 | 1985-04-23 | Balko Alexander B | Process for restoring patency to body vessels |
US4503569A (en) | 1983-03-03 | 1985-03-12 | Dotter Charles T | Transluminally placed expandable graft prosthesis |
US4774949A (en) | 1983-06-14 | 1988-10-04 | Fogarty Thomas J | Deflector guiding catheter |
US4560374A (en) | 1983-10-17 | 1985-12-24 | Hammerslag Julius G | Method for repairing stenotic vessels |
US4616652A (en) | 1983-10-19 | 1986-10-14 | Advanced Cardiovascular Systems, Inc. | Dilatation catheter positioning apparatus |
US4787899A (en) | 1983-12-09 | 1988-11-29 | Lazarus Harrison M | Intraluminal graft device, system and method |
US5275622A (en) | 1983-12-09 | 1994-01-04 | Harrison Medical Technologies, Inc. | Endovascular grafting apparatus, system and method and devices for use therewith |
US5104399A (en) | 1986-12-10 | 1992-04-14 | Endovascular Technologies, Inc. | Artificial graft and implantation method |
US5108424A (en) | 1984-01-30 | 1992-04-28 | Meadox Medicals, Inc. | Collagen-impregnated dacron graft |
US5197977A (en) | 1984-01-30 | 1993-03-30 | Meadox Medicals, Inc. | Drug delivery collagen-impregnated synthetic vascular graft |
US4617932A (en) | 1984-04-25 | 1986-10-21 | Elliot Kornberg | Device and method for performing an intraluminal abdominal aortic aneurysm repair |
US4562596A (en) | 1984-04-25 | 1986-01-07 | Elliot Kornberg | Aortic graft, device and method for performing an intraluminal abdominal aortic aneurysm repair |
SU1217402A1 (en) | 1984-05-22 | 1986-03-15 | Харьковский научно-исследовательский институт общей и неотложной хирургии | Blood vessel prosthesis |
DK151404C (en) | 1984-05-23 | 1988-07-18 | Cook Europ Aps William | FULLY FILTER FOR IMPLANTATION IN A PATIENT'S BLOOD |
SU1318235A1 (en) | 1984-07-10 | 1987-06-23 | Харьковский научно-исследовательский институт общей и неотложной хирургии | Arrangement for fitting a prosthesis into a blood vessel |
US4580568A (en) | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4728328A (en) | 1984-10-19 | 1988-03-01 | Research Corporation | Cuffed tubular organic prostheses |
US4577631A (en) | 1984-11-16 | 1986-03-25 | Kreamer Jeffry W | Aneurysm repair apparatus and method |
US5037377A (en) | 1984-11-28 | 1991-08-06 | Medtronic, Inc. | Means for improving biocompatibility of implants, particularly of vascular grafts |
IT1186142B (en) | 1984-12-05 | 1987-11-18 | Medinvent Sa | TRANSLUMINAL IMPLANTATION DEVICE |
SE450809B (en) | 1985-04-10 | 1987-08-03 | Medinvent Sa | PLANT TOPIC PROVIDED FOR MANUFACTURING A SPIRAL SPRING SUITABLE FOR TRANSLUMINAL IMPLANTATION AND MANUFACTURED SPIRAL SPRINGS |
US4706671A (en) | 1985-05-02 | 1987-11-17 | Weinrib Harry P | Catheter with coiled tip |
US4652263A (en) | 1985-06-20 | 1987-03-24 | Atrium Medical Corporation | Elasticization of microporous woven tubes |
US5242394A (en) | 1985-07-30 | 1993-09-07 | Advanced Cardiovascular Systems, Inc. | Steerable dilatation catheter |
US4923464A (en) | 1985-09-03 | 1990-05-08 | Becton, Dickinson And Company | Percutaneously deliverable intravascular reconstruction prosthesis |
US4650466A (en) | 1985-11-01 | 1987-03-17 | Angiobrade Partners | Angioplasty device |
US5102417A (en) | 1985-11-07 | 1992-04-07 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US4733665C2 (en) | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
DE3640745A1 (en) | 1985-11-30 | 1987-06-04 | Ernst Peter Prof Dr M Strecker | Catheter for producing or extending connections to or between body cavities |
US4681110A (en) | 1985-12-02 | 1987-07-21 | Wiktor Dominik M | Catheter arrangement having a blood vessel liner, and method of using it |
US4817624A (en) | 1985-12-20 | 1989-04-04 | The General Hospital Corporation | Mini-bolus technique for thermodilution cardiac output measurements |
US4665918A (en) | 1986-01-06 | 1987-05-19 | Garza Gilbert A | Prosthesis system and method |
US4693249A (en) | 1986-01-10 | 1987-09-15 | Schenck Robert R | Anastomosis device and method |
US4649922A (en) | 1986-01-23 | 1987-03-17 | Wiktor Donimik M | Catheter arrangement having a variable diameter tip and spring prosthesis |
US4767418A (en) | 1986-02-13 | 1988-08-30 | California Institute Of Technology | Luminal surface fabrication for cardiovascular prostheses |
EP0556940A1 (en) | 1986-02-24 | 1993-08-25 | Robert E. Fischell | Intravascular stent |
JPH0757245B2 (en) | 1986-03-14 | 1995-06-21 | 日本シヤ−ウツド株式会社 | Double tube enteral feeding tube with removable sheath tube and bifurcated connector |
US4878906A (en) | 1986-03-25 | 1989-11-07 | Servetus Partnership | Endoprosthesis for repairing a damaged vessel |
JPS62235496A (en) | 1986-04-04 | 1987-10-15 | Hitachi Chem Co Ltd | Production of substrate having resist pattern |
US5061273A (en) | 1989-06-01 | 1991-10-29 | Yock Paul G | Angioplasty apparatus facilitating rapid exchanges |
SE453258B (en) | 1986-04-21 | 1988-01-25 | Medinvent Sa | ELASTIC, SELF-EXPANDING PROTEST AND PROCEDURE FOR ITS MANUFACTURING |
US4740207A (en) | 1986-09-10 | 1988-04-26 | Kreamer Jeffry W | Intralumenal graft |
SU1482714A2 (en) | 1986-10-15 | 1989-05-30 | Харьковский научно-исследовательский институт общей и неотложной хирургии | Device for setting prosthesis into blood vessel |
SE455834B (en) | 1986-10-31 | 1988-08-15 | Medinvent Sa | DEVICE FOR TRANSLUMINAL IMPLANTATION OF A PRINCIPLE RODFORMALLY RADIALLY EXPANDABLE PROSTHESIS |
US4793348A (en) | 1986-11-15 | 1988-12-27 | Palmaz Julio C | Balloon expandable vena cava filter to prevent migration of lower extremity venous clots into the pulmonary circulation |
US4887997A (en) | 1986-11-21 | 1989-12-19 | Sherwood Medical Company | Catheter for nasogastric intubation |
SU1389778A2 (en) | 1986-11-26 | 1988-04-23 | Харьковский научно-исследовательский институт общей и неотложной хирургии | Arrangement for fitting a prosthesis into blood vessel |
US4762128A (en) | 1986-12-09 | 1988-08-09 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
US4893623A (en) | 1986-12-09 | 1990-01-16 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
US4748982A (en) | 1987-01-06 | 1988-06-07 | Advanced Cardiovascular Systems, Inc. | Reinforced balloon dilatation catheter with slitted exchange sleeve and method |
IT1202558B (en) | 1987-02-17 | 1989-02-09 | Alberto Arpesani | INTERNAL PROSTHESIS FOR THE REPLACEMENT OF A PART OF THE HUMAN BODY PARTICULARLY IN THE VASCULAR OPERATIONS |
US4988356A (en) | 1987-02-27 | 1991-01-29 | C. R. Bard, Inc. | Catheter and guidewire exchange system |
SU1457921A1 (en) | 1987-03-10 | 1989-02-15 | Харьковский научно-исследовательский институт общей и неотложной хирургии | Self-fixing prosthesis of blood vessel |
US5041126A (en) | 1987-03-13 | 1991-08-20 | Cook Incorporated | Endovascular stent and delivery system |
US4907336A (en) | 1987-03-13 | 1990-03-13 | Cook Incorporated | Method of making an endovascular stent and delivery system |
US4800882A (en) | 1987-03-13 | 1989-01-31 | Cook Incorporated | Endovascular stent and delivery system |
JPS63238872A (en) | 1987-03-25 | 1988-10-04 | テルモ株式会社 | Instrument for securing inner diameter of cavity of tubular organ and catheter equipped therewith |
JPS63246178A (en) | 1987-04-01 | 1988-10-13 | 古川 勇一 | Apuncture needle equipped with dilator for imaging blood vessel |
US4795465A (en) | 1987-05-14 | 1989-01-03 | Hood Laboratories | Tracheobronchial stent |
US4872874A (en) | 1987-05-29 | 1989-10-10 | Taheri Syde A | Method and apparatus for transarterial aortic graft insertion and implantation |
US5059211A (en) | 1987-06-25 | 1991-10-22 | Duke University | Absorbable vascular stent |
US4795458A (en) | 1987-07-02 | 1989-01-03 | Regan Barrie F | Stent for use following balloon angioplasty |
US4969458A (en) | 1987-07-06 | 1990-11-13 | Medtronic, Inc. | Intracoronary stent and method of simultaneous angioplasty and stent implant |
JPH088933B2 (en) | 1987-07-10 | 1996-01-31 | 日本ゼオン株式会社 | Catheter |
JPS6446477A (en) | 1987-08-13 | 1989-02-20 | Terumo Corp | Catheter |
DK163713C (en) | 1987-09-02 | 1992-09-07 | Ole Gyring Nieben | DEVICE FOR THE POSITION OF A PARTICULAR CATHETTE IN A BODY |
JPS6483685A (en) | 1987-09-26 | 1989-03-29 | Dainippon Printing Co Ltd | Masking method for minute working |
US4921479A (en) | 1987-10-02 | 1990-05-01 | Joseph Grayzel | Catheter sheath with longitudinal seam |
WO1989003197A1 (en) | 1987-10-08 | 1989-04-20 | Terumo Kabushiki Kaisha | Instrument and apparatus for securing inner diameter of lumen of tubular organ |
US4886062A (en) | 1987-10-19 | 1989-12-12 | Medtronic, Inc. | Intravascular radially expandable stent and method of implant |
US5133732A (en) | 1987-10-19 | 1992-07-28 | Medtronic, Inc. | Intravascular stent |
US5192307A (en) | 1987-12-08 | 1993-03-09 | Wall W Henry | Angioplasty stent |
FR2624747A1 (en) | 1987-12-18 | 1989-06-23 | Delsanti Gerard | REMOVABLE ENDO-ARTERIAL DEVICES FOR REPAIRING ARTERIAL WALL DECOLLEMENTS |
US4870966A (en) | 1988-02-01 | 1989-10-03 | American Cyanamid Company | Bioabsorbable surgical device for treating nerve defects |
US4877030A (en) | 1988-02-02 | 1989-10-31 | Andreas Beck | Device for the widening of blood vessels |
US4892539A (en) | 1988-02-08 | 1990-01-09 | D-R Medical Systems, Inc. | Vascular graft |
US5192311A (en) | 1988-04-25 | 1993-03-09 | Angeion Corporation | Medical implant and method of making |
US4986831A (en) | 1988-04-25 | 1991-01-22 | Angeion Corporation | Medical implant |
US5423745A (en) | 1988-04-28 | 1995-06-13 | Research Medical, Inc. | Irregular surface balloon catheters for body passageways and methods of use |
US4830003A (en) | 1988-06-17 | 1989-05-16 | Wolff Rodney G | Compressive stent and delivery system |
US5226913A (en) | 1988-09-01 | 1993-07-13 | Corvita Corporation | Method of making a radially expandable prosthesis |
US5019090A (en) | 1988-09-01 | 1991-05-28 | Corvita Corporation | Radially expandable endoprosthesis and the like |
US5092877A (en) | 1988-09-01 | 1992-03-03 | Corvita Corporation | Radially expandable endoprosthesis |
US4943346A (en) | 1988-09-29 | 1990-07-24 | Siemens Aktiengesellschaft | Method for manufacturing printed circuit boards |
CA1322628C (en) | 1988-10-04 | 1993-10-05 | Richard A. Schatz | Expandable intraluminal graft |
US4963022A (en) | 1988-10-24 | 1990-10-16 | Zygo Corporation | Method and apparatus for generating a straight reference line |
US5019085A (en) | 1988-10-25 | 1991-05-28 | Cordis Corporation | Apparatus and method for placement of a stent within a subject vessel |
US4913141A (en) | 1988-10-25 | 1990-04-03 | Cordis Corporation | Apparatus and method for placement of a stent within a subject vessel |
US4950227A (en) | 1988-11-07 | 1990-08-21 | Boston Scientific Corporation | Stent delivery system |
US5127919A (en) | 1988-12-14 | 1992-07-07 | Vascutec Corporation | Woven vascular graft |
US4856516A (en) | 1989-01-09 | 1989-08-15 | Cordis Corporation | Endovascular stent apparatus and method |
US4969896A (en) | 1989-02-01 | 1990-11-13 | Interpore International | Vascular graft prosthesis and method of making the same |
US5078726A (en) | 1989-02-01 | 1992-01-07 | Kreamer Jeffry W | Graft stent and method of repairing blood vessels |
US5163958A (en) | 1989-02-02 | 1992-11-17 | Cordis Corporation | Carbon coated tubular endoprosthesis |
US5007926A (en) | 1989-02-24 | 1991-04-16 | The Trustees Of The University Of Pennsylvania | Expandable transluminally implantable tubular prosthesis |
US6146358A (en) | 1989-03-14 | 2000-11-14 | Cordis Corporation | Method and apparatus for delivery of therapeutic agent |
NZ228382A (en) | 1989-03-17 | 1992-08-26 | Carter Holt Harvey Plastic Pro | Drug administering coil-like device for insertion in body cavity of animal |
JP2838291B2 (en) | 1989-03-27 | 1998-12-16 | 日本ゼオン株式会社 | Biological dilator and catheter |
JPH039746A (en) | 1989-03-27 | 1991-01-17 | Olympus Optical Co Ltd | In vivo stay type stent |
US5178634A (en) | 1989-03-31 | 1993-01-12 | Wilson Ramos Martinez | Aortic valved tubes for human implants |
US5100429A (en) | 1989-04-28 | 1992-03-31 | C. R. Bard, Inc. | Endovascular stent and delivery system |
US4990155A (en) | 1989-05-19 | 1991-02-05 | Wilkoff Howard M | Surgical stent method and apparatus |
US4994071A (en) | 1989-05-22 | 1991-02-19 | Cordis Corporation | Bifurcating stent apparatus and method |
US5116318A (en) | 1989-06-06 | 1992-05-26 | Cordis Corporation | Dilatation balloon within an elastic sleeve |
US5037392A (en) | 1989-06-06 | 1991-08-06 | Cordis Corporation | Stent-implanting balloon assembly |
US5015253A (en) | 1989-06-15 | 1991-05-14 | Cordis Corporation | Non-woven endoprosthesis |
US5171262A (en) | 1989-06-15 | 1992-12-15 | Cordis Corporation | Non-woven endoprosthesis |
US5084065A (en) | 1989-07-10 | 1992-01-28 | Corvita Corporation | Reinforced graft assembly |
DE9010130U1 (en) | 1989-07-13 | 1990-09-13 | American Medical Systems, Inc., Minnetonka, Minn., Us | |
US5292331A (en) | 1989-08-24 | 1994-03-08 | Applied Vascular Engineering, Inc. | Endovascular support device |
US5002560A (en) | 1989-09-08 | 1991-03-26 | Advanced Cardiovascular Systems, Inc. | Expandable cage catheter with a rotatable guide |
US5180368A (en) | 1989-09-08 | 1993-01-19 | Advanced Cardiovascular Systems, Inc. | Rapidly exchangeable and expandable cage catheter for repairing damaged blood vessels |
US5034001A (en) | 1989-09-08 | 1991-07-23 | Advanced Cardiovascular Systems, Inc. | Method of repairing a damaged blood vessel with an expandable cage catheter |
CA2026604A1 (en) | 1989-10-02 | 1991-04-03 | Rodney G. Wolff | Articulated stent |
US5035706A (en) | 1989-10-17 | 1991-07-30 | Cook Incorporated | Percutaneous stent and method for retrieval thereof |
US5147385A (en) | 1989-11-01 | 1992-09-15 | Schneider (Europe) A.G. | Stent and catheter for the introduction of the stent |
GB8925380D0 (en) | 1989-11-09 | 1989-12-28 | Leonard Ian | Producing prostheses |
US5089006A (en) | 1989-11-29 | 1992-02-18 | Stiles Frank B | Biological duct liner and installation catheter |
ATE120377T1 (en) | 1990-02-08 | 1995-04-15 | Howmedica | INFLATABLE DILATATOR. |
US5108416A (en) | 1990-02-13 | 1992-04-28 | C. R. Bard, Inc. | Stent introducer system |
US5545208A (en) | 1990-02-28 | 1996-08-13 | Medtronic, Inc. | Intralumenal drug eluting prosthesis |
US5071407A (en) | 1990-04-12 | 1991-12-10 | Schneider (U.S.A.) Inc. | Radially expandable fixation member |
US5221261A (en) | 1990-04-12 | 1993-06-22 | Schneider (Usa) Inc. | Radially expandable fixation member |
US5344426A (en) | 1990-04-25 | 1994-09-06 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5242399A (en) | 1990-04-25 | 1993-09-07 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5158548A (en) | 1990-04-25 | 1992-10-27 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5123917A (en) | 1990-04-27 | 1992-06-23 | Lee Peter Y | Expandable intraluminal vascular graft |
US5078720A (en) | 1990-05-02 | 1992-01-07 | American Medical Systems, Inc. | Stent placement instrument and method |
US5078736A (en) | 1990-05-04 | 1992-01-07 | Interventional Thermodynamics, Inc. | Method and apparatus for maintaining patency in the body passages |
US5578071A (en) | 1990-06-11 | 1996-11-26 | Parodi; Juan C. | Aortic graft |
EP0461791B1 (en) | 1990-06-11 | 1997-01-02 | Hector D. Barone | Aortic graft and apparatus for repairing an abdominal aortic aneurysm |
US5360443A (en) | 1990-06-11 | 1994-11-01 | Barone Hector D | Aortic graft for repairing an abdominal aortic aneurysm |
US5156619A (en) | 1990-06-15 | 1992-10-20 | Ehrenfeld William K | Flanged end-to-side vascular graft |
US5064435A (en) | 1990-06-28 | 1991-11-12 | Schneider (Usa) Inc. | Self-expanding prosthesis having stable axial length |
US5122154A (en) | 1990-08-15 | 1992-06-16 | Rhodes Valentine J | Endovascular bypass graft |
US5217482A (en) | 1990-08-28 | 1993-06-08 | Scimed Life Systems, Inc. | Balloon catheter with distal guide wire lumen |
US5178630A (en) | 1990-08-28 | 1993-01-12 | Meadox Medicals, Inc. | Ravel-resistant, self-supporting woven graft |
US5163952A (en) | 1990-09-14 | 1992-11-17 | Michael Froix | Expandable polymeric stent with memory and delivery apparatus and method |
US5108417A (en) | 1990-09-14 | 1992-04-28 | Interface Biomedical Laboratories Corp. | Anti-turbulent, anti-thrombogenic intravascular stent |
US5222971A (en) | 1990-10-09 | 1993-06-29 | Scimed Life Systems, Inc. | Temporary stent and methods for use and manufacture |
DE69118083T2 (en) | 1990-10-09 | 1996-08-22 | Cook Inc | Percutaneous stent assembly |
DE69116130T2 (en) | 1990-10-18 | 1996-05-15 | Ho Young Song | SELF-EXPANDING, ENDOVASCULAR DILATATOR |
US5161547A (en) | 1990-11-28 | 1992-11-10 | Numed, Inc. | Method of forming an intravascular radially expandable stent |
US5163951A (en) | 1990-12-27 | 1992-11-17 | Corvita Corporation | Mesh composite graft |
US5116360A (en) | 1990-12-27 | 1992-05-26 | Corvita Corporation | Mesh composite graft |
CA2060067A1 (en) | 1991-01-28 | 1992-07-29 | Lilip Lau | Stent delivery system |
US5135536A (en) | 1991-02-05 | 1992-08-04 | Cordis Corporation | Endovascular stent and method |
US5073694A (en) | 1991-02-21 | 1991-12-17 | Synthes (U.S.A.) | Method and apparatus for laser cutting a hollow metal workpiece |
US5116365A (en) | 1991-02-22 | 1992-05-26 | Cordis Corporation | Stent apparatus and method for making |
US5197978B1 (en) | 1991-04-26 | 1996-05-28 | Advanced Coronary Tech | Removable heat-recoverable tissue supporting device |
US5304200A (en) | 1991-05-29 | 1994-04-19 | Cordis Corporation | Welded radially expandable endoprosthesis and the like |
US5234416A (en) | 1991-06-06 | 1993-08-10 | Advanced Cardiovascular Systems, Inc. | Intravascular catheter with a nontraumatic distal tip |
FR2677872A1 (en) | 1991-06-19 | 1992-12-24 | Celsa Lg | Device for assisting in the positioning of a filter for trapping thrombi |
US5314472A (en) | 1991-10-01 | 1994-05-24 | Cook Incorporated | Vascular stent |
US5304220A (en) | 1991-07-03 | 1994-04-19 | Maginot Thomas J | Method and apparatus for implanting a graft prosthesis in the body of a patient |
US5356433A (en) | 1991-08-13 | 1994-10-18 | Cordis Corporation | Biocompatible metal surfaces |
US5197976A (en) | 1991-09-16 | 1993-03-30 | Atrium Medical Corporation | Manually separable multi-lumen vascular graft |
US5183085A (en) | 1991-09-27 | 1993-02-02 | Hans Timmermans | Method and apparatus for compressing a stent prior to insertion |
US5443498A (en) | 1991-10-01 | 1995-08-22 | Cook Incorporated | Vascular stent and method of making and implanting a vacsular stent |
US5242452A (en) | 1991-10-11 | 1993-09-07 | Kanji Inoue | Device for collapsing an appliance collapsible for insertion into human organs |
US5290305A (en) | 1991-10-11 | 1994-03-01 | Kanji Inoue | Appliance collapsible for insertion into human organs and capable of resilient restoration |
AU669338B2 (en) | 1991-10-25 | 1996-06-06 | Cook Incorporated | Expandable transluminal graft prosthesis for repair of aneurysm and method for implanting |
US5720776A (en) | 1991-10-25 | 1998-02-24 | Cook Incorporated | Barb and expandable transluminal graft prosthesis for repair of aneurysm |
US5693084A (en) | 1991-10-25 | 1997-12-02 | Cook Incorporated | Expandable transluminal graft prosthesis for repair of aneurysm |
CA2380683C (en) | 1991-10-28 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
US5372600A (en) | 1991-10-31 | 1994-12-13 | Instent Inc. | Stent delivery systems |
FR2683449A1 (en) | 1991-11-08 | 1993-05-14 | Cardon Alain | ENDOPROTHESIS FOR TRANSLUMINAL IMPLANTATION. |
US5713363A (en) | 1991-11-08 | 1998-02-03 | Mayo Foundation For Medical Education And Research | Ultrasound catheter and method for imaging and hemodynamic monitoring |
US5192297A (en) | 1991-12-31 | 1993-03-09 | Medtronic, Inc. | Apparatus and method for placement and implantation of a stent |
US5484449A (en) | 1992-01-07 | 1996-01-16 | Medtronic, Inc. | Temporary support for a body lumen and method |
US5316023A (en) | 1992-01-08 | 1994-05-31 | Expandable Grafts Partnership | Method for bilateral intra-aortic bypass |
CA2087132A1 (en) | 1992-01-31 | 1993-08-01 | Michael S. Williams | Stent capable of attachment within a body lumen |
US5282823A (en) | 1992-03-19 | 1994-02-01 | Medtronic, Inc. | Intravascular radially expandable stent |
US5368566A (en) | 1992-04-29 | 1994-11-29 | Cardiovascular Dynamics, Inc. | Delivery and temporary stent catheter having a reinforced perfusion lumen |
US5354308A (en) | 1992-05-01 | 1994-10-11 | Beth Israel Hospital Association | Metal wire stent |
US5405378A (en) | 1992-05-20 | 1995-04-11 | Strecker; Ernst P. | Device with a prosthesis implantable in the body of a patient |
US5290295A (en) | 1992-07-15 | 1994-03-01 | Querals & Fine, Inc. | Insertion tool for an intraluminal graft procedure |
US5653690A (en) | 1992-12-30 | 1997-08-05 | Medtronic, Inc. | Catheter having a balloon with retention enhancement |
US5487730A (en) | 1992-12-30 | 1996-01-30 | Medtronic, Inc. | Balloon catheter with balloon surface retention means |
US5360401A (en) | 1993-02-18 | 1994-11-01 | Advanced Cardiovascular Systems, Inc. | Catheter for stent delivery |
WO1994023786A1 (en) | 1993-04-13 | 1994-10-27 | Boston Scientific Corporation | Prosthesis delivery system |
US5458615A (en) | 1993-07-06 | 1995-10-17 | Advanced Cardiovascular Systems, Inc. | Stent delivery system |
GB2281865B (en) | 1993-09-16 | 1997-07-30 | Cordis Corp | Endoprosthesis having multiple laser welded junctions,method and procedure |
US5639278A (en) | 1993-10-21 | 1997-06-17 | Corvita Corporation | Expandable supportive bifurcated endoluminal grafts |
US5571135A (en) | 1993-10-22 | 1996-11-05 | Scimed Life Systems Inc. | Stent delivery apparatus and method |
US5445646A (en) | 1993-10-22 | 1995-08-29 | Scimed Lifesystems, Inc. | Single layer hydraulic sheath stent delivery apparatus and method |
DE69419877T2 (en) | 1993-11-04 | 1999-12-16 | Bard Inc C R | Fixed vascular prosthesis |
AU1091095A (en) | 1993-11-08 | 1995-05-29 | Harrison M. Lazarus | Intraluminal vascular graft and method |
US5443497A (en) | 1993-11-22 | 1995-08-22 | The Johns Hopkins University | Percutaneous prosthetic by-pass graft and method of use |
DE9319267U1 (en) | 1993-12-15 | 1994-02-24 | Vorwerk Dierk Dr | Aortic endoprosthesis |
US5545132A (en) | 1993-12-21 | 1996-08-13 | C. R. Bard, Inc. | Helically grooved balloon for dilatation catheter and method of using |
JP2703510B2 (en) | 1993-12-28 | 1998-01-26 | アドヴァンスド カーディオヴァスキュラー システムズ インコーポレーテッド | Expandable stent and method of manufacturing the same |
US5609627A (en) | 1994-02-09 | 1997-03-11 | Boston Scientific Technology, Inc. | Method for delivering a bifurcated endoluminal prosthesis |
US5507769A (en) | 1994-10-18 | 1996-04-16 | Stentco, Inc. | Method and apparatus for forming an endoluminal bifurcated graft |
SI0821920T2 (en) | 1994-02-25 | 2006-08-31 | Fischell Robert | Stent |
US5449373A (en) | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
US5733303A (en) | 1994-03-17 | 1998-03-31 | Medinol Ltd. | Flexible expandable stent |
US5456694A (en) | 1994-05-13 | 1995-10-10 | Stentco, Inc. | Device for delivering and deploying intraluminal devices |
US5575817A (en) | 1994-08-19 | 1996-11-19 | Martin; Eric C. | Aorto femoral bifurcation graft and method of implantation |
US5609605A (en) | 1994-08-25 | 1997-03-11 | Ethicon, Inc. | Combination arterial stent |
US5527355A (en) | 1994-09-02 | 1996-06-18 | Ahn; Sam S. | Apparatus and method for performing aneurysm repair |
US5836965A (en) | 1994-10-19 | 1998-11-17 | Jendersee; Brad | Stent delivery and deployment method |
US5817152A (en) | 1994-10-19 | 1998-10-06 | Birdsall; Matthew | Connected stent apparatus |
JP2911763B2 (en) | 1994-10-27 | 1999-06-23 | 三桜子 布川 | Artificial blood vessel |
USD376011S (en) | 1994-10-27 | 1996-11-26 | Mioko Nunokawa | Synthetic vascular prosthesis |
CA2134997C (en) | 1994-11-03 | 2009-06-02 | Ian M. Penn | Stent |
CA2175720C (en) | 1996-05-03 | 2011-11-29 | Ian M. Penn | Bifurcated stent and method for the manufacture and delivery of same |
US5800521A (en) | 1994-11-09 | 1998-09-01 | Endotex Interventional Systems, Inc. | Prosthetic graft and method for aneurysm repair |
FR2727969B1 (en) | 1994-12-09 | 1997-01-17 | Roussel Uclaf | NOVEL ERYTHROMYCIN DERIVATIVES, THEIR PREPARATION PROCESS AND THEIR APPLICATION AS MEDICAMENTS |
US5613980A (en) | 1994-12-22 | 1997-03-25 | Chauhan; Tusharsindhu C. | Bifurcated catheter system and method |
NL9500094A (en) | 1995-01-19 | 1996-09-02 | Industrial Res Bv | Y-shaped stent and method of deployment. |
US5755770A (en) | 1995-01-31 | 1998-05-26 | Boston Scientific Corporatiion | Endovascular aortic graft |
BE1009085A3 (en) | 1995-02-10 | 1996-11-05 | De Fays Robert Dr | Intra-aortic prosthesis and surgical instruments for the introduction, implementation and fixing in the aortic prosthesis. |
US5683449A (en) | 1995-02-24 | 1997-11-04 | Marcade; Jean Paul | Modular bifurcated intraluminal grafts and methods for delivering and assembling same |
EP0813397A4 (en) | 1995-03-10 | 1999-10-06 | Cardiovascular Concepts Inc | Tubular endoluminar prosthesis having oblique ends |
US5709713A (en) | 1995-03-31 | 1998-01-20 | Cardiovascular Concepts, Inc. | Radially expansible vascular prosthesis having reversible and other locking structures |
FR2733682B1 (en) | 1995-05-04 | 1997-10-31 | Dibie Alain | ENDOPROSTHESIS FOR THE TREATMENT OF STENOSIS ON BIFURCATIONS OF BLOOD VESSELS AND LAYING EQUIPMENT THEREFOR |
US5591228A (en) | 1995-05-09 | 1997-01-07 | Edoga; John K. | Methods for treating abdominal aortic aneurysms |
FR2737969B1 (en) | 1995-08-24 | 1998-01-30 | Rieu Regis | INTRALUMINAL ENDOPROSTHESIS IN PARTICULAR FOR ANGIOPLASTY |
US5669924A (en) | 1995-10-26 | 1997-09-23 | Shaknovich; Alexander | Y-shuttle stent assembly for bifurcating vessels and method of using the same |
US5591195A (en) | 1995-10-30 | 1997-01-07 | Taheri; Syde | Apparatus and method for engrafting a blood vessel |
FR2740346A1 (en) | 1995-10-30 | 1997-04-30 | Debiotech Sa | ANGIOPLASTY DEVICE FOR ARTERIAL BIFURCATION |
US5626604A (en) | 1995-12-05 | 1997-05-06 | Cordis Corporation | Hand held stent crimping device |
US5690642A (en) | 1996-01-18 | 1997-11-25 | Cook Incorporated | Rapid exchange stent delivery balloon catheter |
CA2192520A1 (en) | 1996-03-05 | 1997-09-05 | Ian M. Penn | Expandable stent and method for delivery of same |
US5713949A (en) | 1996-08-06 | 1998-02-03 | Jayaraman; Swaminathan | Microporous covered stents and method of coating |
US5653691A (en) | 1996-04-25 | 1997-08-05 | Rupp; Garry Eugene | Thickened inner lumen for uniform stent expansion and method of making |
UA58485C2 (en) | 1996-05-03 | 2003-08-15 | Медінол Лтд. | Method for manufacture of bifurcated stent (variants) and bifurcated stent (variants) |
WO1997045073A1 (en) | 1996-05-31 | 1997-12-04 | Bard Galway Limited | Bifurcated endovascular stents and method and apparatus for their placement |
US5617878A (en) | 1996-05-31 | 1997-04-08 | Taheri; Syde A. | Stent and method for treatment of aortic occlusive disease |
US5676697A (en) | 1996-07-29 | 1997-10-14 | Cardiovascular Dynamics, Inc. | Two-piece, bifurcated intraluminal graft for repair of aneurysm |
US5830217A (en) | 1996-08-09 | 1998-11-03 | Thomas J. Fogarty | Soluble fixation device and method for stent delivery catheters |
US6447539B1 (en) * | 1996-09-16 | 2002-09-10 | Transvascular, Inc. | Method and apparatus for treating ischemic heart disease by providing transvenous myocardial perfusion |
US5749825A (en) | 1996-09-18 | 1998-05-12 | Isostent, Inc. | Means method for treatment of stenosed arterial bifurcations |
EP1723931B1 (en) | 1996-11-04 | 2012-01-04 | Advanced Stent Technologies, Inc. | Extendible stent apparatus and method for deploying the same |
US5720735A (en) | 1997-02-12 | 1998-02-24 | Dorros; Gerald | Bifurcated endovascular catheter |
US6096073A (en) | 1997-02-25 | 2000-08-01 | Scimed Life Systems, Inc. | Method of deploying a stent at a lesion site located at a bifurcation in a parent vessel |
EP1011528A1 (en) | 1997-02-25 | 2000-06-28 | SciMed Life Systems, Inc. | Stents and stent delivery and dilatation system for bifurcation lesions |
US5810871A (en) | 1997-04-29 | 1998-09-22 | Medtronic, Inc. | Stent delivery system |
US5913895A (en) | 1997-06-02 | 1999-06-22 | Isostent, Inc. | Intravascular stent with enhanced rigidity strut members |
US7753950B2 (en) | 1997-08-13 | 2010-07-13 | Advanced Cardiovascular Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
US6165195A (en) | 1997-08-13 | 2000-12-26 | Advanced Cardiovascylar Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
US5893887A (en) | 1997-10-14 | 1999-04-13 | Iowa-India Investments Company Limited | Stent for positioning at junction of bifurcated blood vessel and method of making |
US6179868B1 (en) | 1998-03-27 | 2001-01-30 | Janet Burpee | Stent with reduced shortening |
US5893852A (en) | 1998-04-28 | 1999-04-13 | Advanced Cardiovascular Systems, Inc. | Stent crimping tool and method of use |
AU761192B2 (en) * | 1998-06-10 | 2003-05-29 | Converge Medical, Inc. | Sutureless anastomosis systems |
AU4323199A (en) * | 1998-06-19 | 2000-01-05 | Endologix, Inc. | Self expanding bifurcated endovascular prosthesis |
US6117117A (en) | 1998-08-24 | 2000-09-12 | Advanced Cardiovascular Systems, Inc. | Bifurcated catheter assembly |
US6190403B1 (en) | 1998-11-13 | 2001-02-20 | Cordis Corporation | Low profile radiopaque stent with increased longitudinal flexibility and radial rigidity |
US6733523B2 (en) * | 1998-12-11 | 2004-05-11 | Endologix, Inc. | Implantable vascular graft |
US6752813B2 (en) | 1999-04-09 | 2004-06-22 | Evalve, Inc. | Methods and devices for capturing and fixing leaflets in valve repair |
US8579966B2 (en) * | 1999-11-17 | 2013-11-12 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
AU1723201A (en) * | 1999-11-18 | 2001-05-30 | Petrus Besselink | Method for placing bifurcated stents |
US6673107B1 (en) * | 1999-12-06 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Bifurcated stent and method of making |
US6821297B2 (en) * | 2000-02-02 | 2004-11-23 | Robert V. Snyders | Artificial heart valve, implantation instrument and method therefor |
US6773454B2 (en) * | 2000-08-02 | 2004-08-10 | Michael H. Wholey | Tapered endovascular stent graft and method of treating abdominal aortic aneurysms and distal iliac aneurysms |
US7691144B2 (en) * | 2003-10-01 | 2010-04-06 | Mvrx, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
US6699278B2 (en) | 2000-09-22 | 2004-03-02 | Cordis Corporation | Stent with optimal strength and radiopacity characteristics |
US6503272B2 (en) | 2001-03-21 | 2003-01-07 | Cordis Corporation | Stent-based venous valves |
US6749628B1 (en) | 2001-05-17 | 2004-06-15 | Advanced Cardiovascular Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
US7018404B2 (en) * | 2002-01-24 | 2006-03-28 | St. Jude Medical, Inc. | Conduit for aorta or pulmonary artery replacement |
US6676699B2 (en) * | 2002-04-26 | 2004-01-13 | Medtronic Ave, Inc | Stent graft with integrated valve device and method |
US7399313B2 (en) * | 2002-06-07 | 2008-07-15 | Brown Peter S | Endovascular graft with separable sensors |
US7241257B1 (en) * | 2002-06-28 | 2007-07-10 | Abbott Cardiovascular Systems, Inc. | Devices and methods to perform minimally invasive surgeries |
WO2004043516A2 (en) * | 2002-11-08 | 2004-05-27 | James Robineau Margolis | Device and method for electrical isolation of the pulmonary veins |
US7250041B2 (en) | 2003-03-12 | 2007-07-31 | Abbott Cardiovascular Systems Inc. | Retrograde pressure regulated infusion |
US7159593B2 (en) * | 2003-04-17 | 2007-01-09 | 3F Therapeutics, Inc. | Methods for reduction of pressure effects of cardiac tricuspid valve regurgitation |
EP2133039B1 (en) * | 2003-04-24 | 2014-10-08 | Cook Medical Technologies LLC | Artificial valve prosthesis with improved flow dynamics |
US7513867B2 (en) * | 2003-07-16 | 2009-04-07 | Kardium, Inc. | Methods and devices for altering blood flow through the left ventricle |
US7559948B2 (en) * | 2003-09-17 | 2009-07-14 | Ricardo Gamboa | Fenestrated asymmetric intracardiac device for the completion of total cavopulmonary anastomosis through cardiac catheterization |
US7374573B2 (en) * | 2004-05-03 | 2008-05-20 | Shlomo Gabbay | System and method for improving ventricular function |
US20060212113A1 (en) * | 2005-02-24 | 2006-09-21 | Shaolian Samuel M | Externally adjustable endovascular graft implant |
SE531468C2 (en) * | 2005-04-21 | 2009-04-14 | Edwards Lifesciences Ag | An apparatus for controlling blood flow |
US7914569B2 (en) | 2005-05-13 | 2011-03-29 | Medtronics Corevalve Llc | Heart valve prosthesis and methods of manufacture and use |
US20070050015A1 (en) * | 2005-08-25 | 2007-03-01 | Scimed Life Systems, Inc. | Endoluminal prosthesis adapted to deployment in a distorted branched body lumen and method of deploying the same |
CA2660892A1 (en) * | 2005-09-09 | 2007-03-15 | Edwards Lifesciences Corporation | Device and method for reshaping mitral valve annulus |
US20070213813A1 (en) * | 2005-12-22 | 2007-09-13 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US7771467B2 (en) * | 2006-11-03 | 2010-08-10 | The Cleveland Clinic Foundation | Apparatus for repairing the function of a native aortic valve |
US8715337B2 (en) * | 2007-11-09 | 2014-05-06 | Cook Medical Technologies Llc | Aortic valve stent graft |
EP2695587A1 (en) * | 2008-01-25 | 2014-02-12 | JenaValve Technology Inc. | Medical apparatus for the therapeutic treatment of an insufficient cardiac valve |
WO2009129481A1 (en) * | 2008-04-18 | 2009-10-22 | Cook Incorporated | Branched vessel prosthesis |
US20090276040A1 (en) * | 2008-05-01 | 2009-11-05 | Edwards Lifesciences Corporation | Device and method for replacing mitral valve |
CN102202582B (en) * | 2008-09-04 | 2014-07-30 | 库拉希尔公司 | Inflatable device for enteric fistula treatment |
US20100217382A1 (en) | 2009-02-25 | 2010-08-26 | Edwards Lifesciences | Mitral valve replacement with atrial anchoring |
US9427302B2 (en) * | 2009-04-09 | 2016-08-30 | Medtronic Vascular, Inc. | Stent having a C-shaped body section for use in a bifurcation |
WO2011005840A2 (en) * | 2009-07-07 | 2011-01-13 | Med Institute, Inc. | Hydrogel enhanced medical devices |
WO2011109450A2 (en) * | 2010-03-01 | 2011-09-09 | Colibri Heart Valve Llc | Percutaneously deliverable heart valve and methods associated therewith |
CA3051684C (en) * | 2011-12-06 | 2020-06-16 | Aortic Innovations Llc | Device for endovascular aortic repair and method of using the same |
US20130158673A1 (en) * | 2011-12-15 | 2013-06-20 | Cook Medical Technologies Llc | Anti-Leakage Prosthesis |
US9023098B2 (en) | 2012-03-28 | 2015-05-05 | Medtronic, Inc. | Dual valve prosthesis for transcatheter valve implantation |
EP2732796A1 (en) | 2012-11-20 | 2014-05-21 | Nakostech Sarl | Mitral valve replacement system |
US9993330B2 (en) * | 2013-03-13 | 2018-06-12 | Cook Medical Technologies Llc | Endoluminal prosthesis system |
US9089414B2 (en) * | 2013-03-22 | 2015-07-28 | Edwards Lifesciences Corporation | Device and method for increasing flow through the left atrial appendage |
EP2929860B1 (en) * | 2014-04-07 | 2017-06-28 | Nvt Ag | Device for implantation in the heart of a mammal |
JP6539678B2 (en) * | 2014-05-30 | 2019-07-03 | エンドロジックス、インク | Modular stent-graft system with expandable filling structure and method of using the same |
PL3184081T3 (en) * | 2015-12-22 | 2021-10-04 | Medira Ag | Prosthetic mitral valve coaptation enhancement device |
US10130465B2 (en) * | 2016-02-23 | 2018-11-20 | Abbott Cardiovascular Systems Inc. | Bifurcated tubular graft for treating tricuspid regurgitation |
EP3578138A1 (en) * | 2016-03-22 | 2019-12-11 | Assistance Publique, Hopitaux De Paris | Vascular valved prosthesis and manufacturing method |
DE102017121143A1 (en) * | 2017-09-13 | 2019-03-14 | Universitätsklinikum Hamburg-Eppendorf (UKE) | Implantable valve prosthesis |
EP3810033A1 (en) * | 2018-06-19 | 2021-04-28 | Medtronic Vascular Inc. | Modular stent device for multiple vessels and method |
-
2016
- 2016-02-23 US US15/051,045 patent/US10130465B2/en active Active
-
2017
- 2017-02-21 WO PCT/US2017/018741 patent/WO2017147082A1/en active Application Filing
-
2018
- 2018-11-16 US US16/193,895 patent/US11051938B2/en active Active
-
2021
- 2021-06-02 US US17/336,542 patent/US11583399B2/en active Active
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060276813A1 (en) * | 2005-05-20 | 2006-12-07 | The Cleveland Clinic Foundation | Apparatus and methods for repairing the function of a diseased valve and method for making same |
US8029558B2 (en) | 2006-07-07 | 2011-10-04 | Abbott Cardiovascular Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
EP2600798B1 (en) * | 2010-08-03 | 2015-10-28 | Cook Medical Technologies LLC | Two valve caval stent for functional replacement of incompetent tricuspid valve |
Cited By (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11185677B2 (en) | 2017-06-07 | 2021-11-30 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
US11717670B2 (en) | 2017-06-07 | 2023-08-08 | Shifamed Holdings, LLP | Intravascular fluid movement devices, systems, and methods of use |
US11511103B2 (en) | 2017-11-13 | 2022-11-29 | Shifamed Holdings, Llc | Intravascular fluid movement devices, systems, and methods of use |
US10722631B2 (en) | 2018-02-01 | 2020-07-28 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of use and manufacture |
US11229784B2 (en) | 2018-02-01 | 2022-01-25 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of use and manufacture |
US11964145B2 (en) | 2019-07-12 | 2024-04-23 | Shifamed Holdings, Llc | Intravascular blood pumps and methods of manufacture and use |
US11654275B2 (en) | 2019-07-22 | 2023-05-23 | Shifamed Holdings, Llc | Intravascular blood pumps with struts and methods of use and manufacture |
US11724089B2 (en) | 2019-09-25 | 2023-08-15 | Shifamed Holdings, Llc | Intravascular blood pump systems and methods of use and control thereof |
WO2021058512A1 (en) | 2019-09-26 | 2021-04-01 | Biotronik Ag | Artificial cardiac valve |
Also Published As
Publication number | Publication date |
---|---|
US20170239043A1 (en) | 2017-08-24 |
US10130465B2 (en) | 2018-11-20 |
US20190083258A1 (en) | 2019-03-21 |
US11583399B2 (en) | 2023-02-21 |
US11051938B2 (en) | 2021-07-06 |
US20210282926A1 (en) | 2021-09-16 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US11583399B2 (en) | Bifurcated tubular graft for treating tricuspid regurgitation | |
US11744699B2 (en) | Heart valve prostheses and methods for percutaneous heart valve replacement | |
US11877926B2 (en) | Prosthetic heart valve devices and associated systems and methods | |
US20200360138A1 (en) | Method and Design for a Mitral Regurgitation Treatment Device | |
US20220015903A1 (en) | Transseptal delivery systems having a deflecting segment and methods of use | |
US10543079B2 (en) | Heart valve prosthesis | |
US9839517B2 (en) | Implantable device for treating mitral valve regurgitation | |
JP6560507B2 (en) | Device for implantation in the heart of a mammal | |
JP2021090836A (en) | Heart valve prostheses having multiple support arms and methods for percutaneous heart valve replacement | |
US20170172737A1 (en) | Prosthetic mitral valve coaptation enhancement device | |
US20120010700A1 (en) | Method for implanting prosthetic valve | |
WO2019128583A1 (en) | Cardiac valve prosthesis and stent thereof | |
US20230218396A1 (en) | Trans-septal delivery system and methods of use | |
CN111195166A (en) | Knittable heart valve device and manufacturing method and using method thereof | |
US11951004B2 (en) | Prosthetic valve device resistant to backfolding and buckling | |
US20240081984A1 (en) | Prosthetic heart valve with non-abrasive outflow region |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
NENP | Non-entry into the national phase |
Ref country code: DE |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 17708946 Country of ref document: EP Kind code of ref document: A1 |
|
122 | Ep: pct application non-entry in european phase |
Ref document number: 17708946 Country of ref document: EP Kind code of ref document: A1 |